CA2330029C - Method of selective photothermolysis - Google Patents
Method of selective photothermolysis Download PDFInfo
- Publication number
- CA2330029C CA2330029C CA2330029A CA2330029A CA2330029C CA 2330029 C CA2330029 C CA 2330029C CA 2330029 A CA2330029 A CA 2330029A CA 2330029 A CA2330029 A CA 2330029A CA 2330029 C CA2330029 C CA 2330029C
- Authority
- CA
- Canada
- Prior art keywords
- electromagnetic radiation
- source
- heat source
- target tissue
- target
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/203—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser applying laser energy to the outside of the body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00017—Electrical control of surgical instruments
- A61B2017/00022—Sensing or detecting at the treatment site
- A61B2017/00057—Light
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00017—Electrical control of surgical instruments
- A61B2017/00137—Details of operation mode
- A61B2017/00154—Details of operation mode pulsed
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
- A61B2018/00452—Skin
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
- A61B2018/00452—Skin
- A61B2018/00458—Deeper parts of the skin, e.g. treatment of vascular disorders or port wine stains
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B2018/1807—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using light other than laser radiation
Abstract
A method and device for selective photothermolysis of a surgical target within surrounding tissue. The target and the surrounding tissue are heated to about 60 ~C. Then the target is heated to the point of coagulation, preferably by monochromatic light. The temperature difference between the coagulating target and the surrounding tissue is sufficiently mild that heat diffusing out of the target does not damage the surrounding tissue, even in the case of a relatively large target such as varicose veins.
Description
METHOD OF SELECTIVE PHOTOTHERMOLYSIS
FIELD AND BACKGROUND
The present invention relates to dermatological surgery and, more specifically, to a method of selective photothermolysis that allows the destruction of targets, such as varicose veins, that are too large to be destroyed by presently known methods without damaging the surrounding healthy tissue.
Selective photothermolysis is a surgical method, introduced by Anderson and Parrish in 1983 ("Selective Photothermolysis: Precise Microsurgery by Selective Absorption of Pulsed Radiation", Science, Vol. 220, pp. 524-527), for destroying certain diseased or unsightly tissue, on or near the skin, with minimal damage to the surrounding healthy tissue. The tissue to be destroyed must be characterized by significantly greater optical absorption at some wavelength of electromagnetic radiation than the surrounding tissue. The method consists of irradiating the target and the surrounding tissue with pulsed electromagnetic radiation, usually visible radiation, that is preferentially absorbed by the target. The energy and duration of the pulses is such that the target is heated to between about 70 C and about 80 C, at which temperature the proteins of the target coagulate. Because the target absorbs the incident radiation much more strongly than the surrounding tissue, the surrounding tissue is heated negligibly.
Usually, the radiation source is a laser, for example a flashlamp-pulsed dye laser. A laser source has the advantage of being inherently monochromatic.
Other sources include broad band sources used in conjunction with narrow band filters, as described, for example, by Gustaffson in Patent No. WO 91/15264. A similar device, called the "Photoderm-VL", is manufactured by ESC Medical Systems.
FIELD AND BACKGROUND
The present invention relates to dermatological surgery and, more specifically, to a method of selective photothermolysis that allows the destruction of targets, such as varicose veins, that are too large to be destroyed by presently known methods without damaging the surrounding healthy tissue.
Selective photothermolysis is a surgical method, introduced by Anderson and Parrish in 1983 ("Selective Photothermolysis: Precise Microsurgery by Selective Absorption of Pulsed Radiation", Science, Vol. 220, pp. 524-527), for destroying certain diseased or unsightly tissue, on or near the skin, with minimal damage to the surrounding healthy tissue. The tissue to be destroyed must be characterized by significantly greater optical absorption at some wavelength of electromagnetic radiation than the surrounding tissue. The method consists of irradiating the target and the surrounding tissue with pulsed electromagnetic radiation, usually visible radiation, that is preferentially absorbed by the target. The energy and duration of the pulses is such that the target is heated to between about 70 C and about 80 C, at which temperature the proteins of the target coagulate. Because the target absorbs the incident radiation much more strongly than the surrounding tissue, the surrounding tissue is heated negligibly.
Usually, the radiation source is a laser, for example a flashlamp-pulsed dye laser. A laser source has the advantage of being inherently monochromatic.
Other sources include broad band sources used in conjunction with narrow band filters, as described, for example, by Gustaffson in Patent No. WO 91/15264. A similar device, called the "Photoderm-VL", is manufactured by ESC Medical Systems.
Suitable targets for selective photothermolysis include birthmarks, port-wine stains, spider veins, and varicose veins, all of which tend to be much redder than the surrounding tissue because of their higher concentration of oxyhemoglobin-containing red blood cells. Anderson and Parrish used light of a wavelength of 577 nanometers, corresponding to the 577 nanometer oxyhemoglobin absorption band. It was subsequently determined (Tian, Morrison, and Kurban, "585 nm for the Treatment of Port-Wine Stains", Plastic and Reconstructive Surgery, vol. 86 no. 6 pp. 1112-1117) that 585 nanometers is a more effective wavelength to use.
One constraint on the pulse duration is that the surrounding tissue must not be heated to the point that it, too, begins to coagulate. As the target is heated, heat begins to diffuse from the target to the cooler surrounding tissue. To keep the surrounding tissue from being heated to the point of damage, the pulse length must be kept on the order of the target's thermal relaxation time. For relatively small targets, such as birthmarks, port-wine stains, and spider veins, typical pulse lengths are on the order of hundreds of microseconds. For varicose veins, pulse lengths on the order of milliseconds should be used.
A complication arises in the treatment of varicose veins by selective photothermolysis. The normal tissue surrounding varicose veins typically includes other blood vessels, notably capillaries, that also absorb the incident radiation but, being much smaller than the varicose veins, have much shorter thermal relaxation times. Therefore, heat diffusing from these other blood vessels into the surrounding tissue tends to heat the surrounding tissue to the point of damage, thereby causing scarring.
One constraint on the pulse duration is that the surrounding tissue must not be heated to the point that it, too, begins to coagulate. As the target is heated, heat begins to diffuse from the target to the cooler surrounding tissue. To keep the surrounding tissue from being heated to the point of damage, the pulse length must be kept on the order of the target's thermal relaxation time. For relatively small targets, such as birthmarks, port-wine stains, and spider veins, typical pulse lengths are on the order of hundreds of microseconds. For varicose veins, pulse lengths on the order of milliseconds should be used.
A complication arises in the treatment of varicose veins by selective photothermolysis. The normal tissue surrounding varicose veins typically includes other blood vessels, notably capillaries, that also absorb the incident radiation but, being much smaller than the varicose veins, have much shorter thermal relaxation times. Therefore, heat diffusing from these other blood vessels into the surrounding tissue tends to heat the surrounding tissue to the point of damage, thereby causing scarring.
There is thus a widely recognized need for, and it would be highly advantageous to have, a method of selective photothermolysis that is effective in removing larger surgical targets, such as varicose veins, without peripheral damage.
SUMMARY OF THE INVENTION
According to the present invention there is provided a method of selective photothermolysis of a target within surrounding tissue, comprising the steps of. (a) heating the target and the surrounding tissue above normal body temperature;
and (b) heating the target to between about 70 C and about 80 C.
According to the present invention there is provided a device for selective photothermolysis of a target within surrounding tissue, comprising: (a) means for generating broad-band electromagnetic radiation; and (b) means for generating at least one pulse of substantially monochromatic electromagnetic radiation, each of said at least one pulse being substantially simultaneous with said broad-band electromagnetic radiation.
The method of the present invention is based on the fact that the rate of heat diffusion from a warm body to a cold body is proportional to the thermal gradient between the bodies. Therefore, heating the surrounding tissue to a temperature higher than normal body temperature, but not high enough to cause damage, and only then heating the target to the point of coagulation, creates an environment in which the thermal gradient between the target and the surrounding blood vessels, on the one hand, and the other surrounding tissue, on the other hand, is sufficiently small that the surrounding tissue is not damaged. In the context of the present invention, "higher than normal body temperature" means a temperature of at least about 40 C, but preferably between about 55 C and about 65 C. Furthermore, the pulse of monochromatic light used to heat the target may be of lower power and shorter duration than in the prior art, because the target is heated from a higher initial temperature.
The device of the present invention accomplishes this end by heating the surrounding tissue using broad-band electromagnetic radiation. The scope of the present invention includes all effective wavelengths of electromagnetic radiation, and effective spectral bands for this purpose include microwave radiation; but the to preferred spectral band, both for heating the surrounding tissue and for heating the target itself, is visible radiation. The preferred device for generating the broad-band (white) light is a high intensity lamp such as a xenon arc lamp. The device includes a mechanism for pulsing the light from the lamp. This mechanism may include circuitry for controlling the current supplied to the lamp (e.g., the mechanism may operate by turning the lamp on and off); or may include a mechanical shutter.
There are two preferred means for generating the substantially monochromatic radiation used to heat the target. The first is a laser that operates at the desired wavelength, preferably a wavelength between about 570 nanometers and about 610 nanometers. The second is to pass light from the high intensity lamp through a suitable wavelength selection device, such as a narrow band filter or a monochromator.
The device of the present invention synchronizes the monochromatic pulses with the broad-band electromagnetic radiation, by means well-known in the art, to ensure that the surrounding tissue has been heated sufficiently before the monochromatic pulse is turned on to heat the target further, and to ensure that the target is heated further before the surrounding tissue has a chance to cool down. In general terms, this means that, if the broad-band electromagnetic radiation is pulsed, 5 then each monochromatic pulse is substantially simultaneous with a broad-band pulse.
As used herein "substantially simultaneous" means that the monochromatic pulse is turned on either while the broad-band pulse is on, or substantially immediately after the broad-band pulse is turned off.
1o BRIEF DESCRIPTION OF THE DRAWINGS
The invention is herein described, by way of example only, with reference to the accompanying drawings, wherein:
FIG. I is a schematic diagram of a preferred embodiment of the device of the present invention in which the source of monochromatic light is a laser;
FIG. 2 shows a pulse schedule for the device of FIG. 1;
FIG. 3 is a schematic diagram of a preferred embodiment of the device of the present invention in which the source of monochromatic light is the same as the source of the broad-band light;
FIG. 4 shows a pulse schedule for the device of FIG. 3;
FIG. 5 shows an alternative embodiment of the device of FIG. 4.
FIG. 6 shows a pulse schedule for the device of FIG. 5.
SUMMARY OF THE INVENTION
According to the present invention there is provided a method of selective photothermolysis of a target within surrounding tissue, comprising the steps of. (a) heating the target and the surrounding tissue above normal body temperature;
and (b) heating the target to between about 70 C and about 80 C.
According to the present invention there is provided a device for selective photothermolysis of a target within surrounding tissue, comprising: (a) means for generating broad-band electromagnetic radiation; and (b) means for generating at least one pulse of substantially monochromatic electromagnetic radiation, each of said at least one pulse being substantially simultaneous with said broad-band electromagnetic radiation.
The method of the present invention is based on the fact that the rate of heat diffusion from a warm body to a cold body is proportional to the thermal gradient between the bodies. Therefore, heating the surrounding tissue to a temperature higher than normal body temperature, but not high enough to cause damage, and only then heating the target to the point of coagulation, creates an environment in which the thermal gradient between the target and the surrounding blood vessels, on the one hand, and the other surrounding tissue, on the other hand, is sufficiently small that the surrounding tissue is not damaged. In the context of the present invention, "higher than normal body temperature" means a temperature of at least about 40 C, but preferably between about 55 C and about 65 C. Furthermore, the pulse of monochromatic light used to heat the target may be of lower power and shorter duration than in the prior art, because the target is heated from a higher initial temperature.
The device of the present invention accomplishes this end by heating the surrounding tissue using broad-band electromagnetic radiation. The scope of the present invention includes all effective wavelengths of electromagnetic radiation, and effective spectral bands for this purpose include microwave radiation; but the to preferred spectral band, both for heating the surrounding tissue and for heating the target itself, is visible radiation. The preferred device for generating the broad-band (white) light is a high intensity lamp such as a xenon arc lamp. The device includes a mechanism for pulsing the light from the lamp. This mechanism may include circuitry for controlling the current supplied to the lamp (e.g., the mechanism may operate by turning the lamp on and off); or may include a mechanical shutter.
There are two preferred means for generating the substantially monochromatic radiation used to heat the target. The first is a laser that operates at the desired wavelength, preferably a wavelength between about 570 nanometers and about 610 nanometers. The second is to pass light from the high intensity lamp through a suitable wavelength selection device, such as a narrow band filter or a monochromator.
The device of the present invention synchronizes the monochromatic pulses with the broad-band electromagnetic radiation, by means well-known in the art, to ensure that the surrounding tissue has been heated sufficiently before the monochromatic pulse is turned on to heat the target further, and to ensure that the target is heated further before the surrounding tissue has a chance to cool down. In general terms, this means that, if the broad-band electromagnetic radiation is pulsed, 5 then each monochromatic pulse is substantially simultaneous with a broad-band pulse.
As used herein "substantially simultaneous" means that the monochromatic pulse is turned on either while the broad-band pulse is on, or substantially immediately after the broad-band pulse is turned off.
1o BRIEF DESCRIPTION OF THE DRAWINGS
The invention is herein described, by way of example only, with reference to the accompanying drawings, wherein:
FIG. I is a schematic diagram of a preferred embodiment of the device of the present invention in which the source of monochromatic light is a laser;
FIG. 2 shows a pulse schedule for the device of FIG. 1;
FIG. 3 is a schematic diagram of a preferred embodiment of the device of the present invention in which the source of monochromatic light is the same as the source of the broad-band light;
FIG. 4 shows a pulse schedule for the device of FIG. 3;
FIG. 5 shows an alternative embodiment of the device of FIG. 4.
FIG. 6 shows a pulse schedule for the device of FIG. 5.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
The present invention is a method and device for selective photothermolysis of relatively large surgical targets. Specifically, the present invention can be used to remove varicose veins and similar diseased or unsightly tissue with minimal damage to the surrounding healthy tissue.
The principles and operation of a method and device for selective photothermolysis according to the present invention may be better understood with 1o reference to the drawings and the accompanying description.
Referring now to the drawings, Figure 1 is a schematic diagram of a preferred embodiment of the device of the present invention. A high intensity lamp 10 functions as a source of broad-band (white) light 14. Because lamp 10 emits light in all directions, a parabolic reflector 12 and a concave lens 16 are provided to collimate broad-band light 14, so that substantially all the energy emitted by lamp 10 is directed at the target and the surrounding tissue. A laser 20 emits substantially monochromatic light 24, preferably at a wavelength of 585 nanometers, also towards the target and the surrounding tissue. A
control system 30 supplies power to lamp 10 and laser 20, and also turns lamp 10 and laser 20 on and off in accordance with the pulse schedule shown in Figure 2.
Preferably, lamp 10 is a xenon arc lamp. Preferably, laser 20 is a flashlamp-pulsed dye laser, for example the ScleroLASER* manufactured by Candela Corporation of Wayland, MA.
Figure 2 shows a pulse schedule for the device of Figure 1. The solid line in Figure 2 represents then duration and intensity of a pulse-band light 14. The * Trade mark dashed line in Figure 2 represents the duration and intensity of a pulse of monochromatic light 24. Broad-band light 14 is turned on at time T0, and is kept on long enough, until time T2, to heat the target and the surrounding tissue to about 60 C.
As the temperature of the surrounding tissue approaches the desired final value, monochromatic light 24 is turned on at time T1, and is kept on until time T3, long enough to cause coagulation of the target but not long enough to damage the surrounding tissue. Preferably, the duration of the monochromatic pulse is between about 0.1 milliseconds and about 10 milliseconds.
Figure 3 is a schematic diagram of another preferred embodiment of the device of the present invention. In this embodiment, lamp 10 serves as the source of both the broad-band radiation and the monochromatic radiation that are incident on the target and the surrounding tissue. In this embodiment, a mechanical shutter 32 serves to alternately block and pass broad-band light 14, thus causing the light emerging from the device to be pulsed. A rotating circular filter 34 having two sections, a white section 36 and a colored section 38, serves to filter the broad-band pulses passed by shutter 32. White section 36 attenuates all wavelengths to substantially the same degree, thereby providing a broad-band pulse of the proper intensity and duration to heat the target and the surrounding tissue to about 60 C. Colored section 38 attenuates all but a narrow spectral band of light centered on a wavelength of nanometers. Control system 30 synchronizes the movement of shutter 32 and filter 34 to provide light pulses according to the pulse schedule of Figure 4.
Note that lamp 10 must be much more powerful in the embodiment of Figure 3 than in the embodiment of Figure 1, because in the embodiment of Figure 3, lamp must provide enough spectral power in the vicinity of 585 nanometers to coagulate the target. It is for this reason that white section 36 of filter 34 is required in this embodiment.
Figure 4 shows a pulse schedule for the device of Figure 3. As in Figure 2, a 5 solid line represents a broad-band pulse and a dashed line represents a monochromatic pulse. At time To, with filter 34 positioned so that white section 36 is in the optical path of broad-band light 14, shutter 32 is opened, allowing broad-band light 14 to pass through, and to be attenuated by, white section 36. Filter 34 is rotated, until, at time T1, colored section 38 begins to intercept broad-band light 14. At time T2, all of 1o broad-band light 14 is passing through colored section 38, so that the light emerging from the device is substantially monochromatic. At time T3, shutter 32 is closed, terminating the monochromatic pulse.
Figure 5 is a schematic diagram of a variant of the device of Figure 3. In the device of Figure 5, a movable mirror 40 is provided to deflect light passed by shutter 32 to a fixed mirror 41 and a monochromator 42. The device of Figure 5 generates pulses according to the pulse schedule of Figure 6, in which, again, the solid line represents a broad-band pulse and the dashed line represents a monochromatic pulse.
At time To, with mirror 40 withdrawn, shutter 32 is opened, allowing broad-band light 14 to pass through an attenuation filter 44 and thence to the target and the surrounding tissue. Like white region 36 of filter 34, attenuation filter 44 attenuates all wavelengths to substantially the same degree, to provide a broad-band pulse of the proper duration and intensity to heat the target and the surrounding tissue to about 60 C. At time T1, mirror 40 is moved into place, terminating the broad-band pulse, and, deflecting broad-band light 14 so that it passes, via mirror 41, through monochromator 42, thereby initiating the monochromatic pulse. Thus, the monochromatic pulse starts substantially immediately after the termination of the broad-band pulse. Monochromator 42 passes on to the target only a narrow spectral band of light centered on a wavelength of 585 nanometers. At time T2, shutter closes, terminating the monochromatic pulse.
While the invention has been described with respect to a limited number of embodiments, it will be appreciated that many variations, modifications, and other applications of the invention may be made.
The present invention is a method and device for selective photothermolysis of relatively large surgical targets. Specifically, the present invention can be used to remove varicose veins and similar diseased or unsightly tissue with minimal damage to the surrounding healthy tissue.
The principles and operation of a method and device for selective photothermolysis according to the present invention may be better understood with 1o reference to the drawings and the accompanying description.
Referring now to the drawings, Figure 1 is a schematic diagram of a preferred embodiment of the device of the present invention. A high intensity lamp 10 functions as a source of broad-band (white) light 14. Because lamp 10 emits light in all directions, a parabolic reflector 12 and a concave lens 16 are provided to collimate broad-band light 14, so that substantially all the energy emitted by lamp 10 is directed at the target and the surrounding tissue. A laser 20 emits substantially monochromatic light 24, preferably at a wavelength of 585 nanometers, also towards the target and the surrounding tissue. A
control system 30 supplies power to lamp 10 and laser 20, and also turns lamp 10 and laser 20 on and off in accordance with the pulse schedule shown in Figure 2.
Preferably, lamp 10 is a xenon arc lamp. Preferably, laser 20 is a flashlamp-pulsed dye laser, for example the ScleroLASER* manufactured by Candela Corporation of Wayland, MA.
Figure 2 shows a pulse schedule for the device of Figure 1. The solid line in Figure 2 represents then duration and intensity of a pulse-band light 14. The * Trade mark dashed line in Figure 2 represents the duration and intensity of a pulse of monochromatic light 24. Broad-band light 14 is turned on at time T0, and is kept on long enough, until time T2, to heat the target and the surrounding tissue to about 60 C.
As the temperature of the surrounding tissue approaches the desired final value, monochromatic light 24 is turned on at time T1, and is kept on until time T3, long enough to cause coagulation of the target but not long enough to damage the surrounding tissue. Preferably, the duration of the monochromatic pulse is between about 0.1 milliseconds and about 10 milliseconds.
Figure 3 is a schematic diagram of another preferred embodiment of the device of the present invention. In this embodiment, lamp 10 serves as the source of both the broad-band radiation and the monochromatic radiation that are incident on the target and the surrounding tissue. In this embodiment, a mechanical shutter 32 serves to alternately block and pass broad-band light 14, thus causing the light emerging from the device to be pulsed. A rotating circular filter 34 having two sections, a white section 36 and a colored section 38, serves to filter the broad-band pulses passed by shutter 32. White section 36 attenuates all wavelengths to substantially the same degree, thereby providing a broad-band pulse of the proper intensity and duration to heat the target and the surrounding tissue to about 60 C. Colored section 38 attenuates all but a narrow spectral band of light centered on a wavelength of nanometers. Control system 30 synchronizes the movement of shutter 32 and filter 34 to provide light pulses according to the pulse schedule of Figure 4.
Note that lamp 10 must be much more powerful in the embodiment of Figure 3 than in the embodiment of Figure 1, because in the embodiment of Figure 3, lamp must provide enough spectral power in the vicinity of 585 nanometers to coagulate the target. It is for this reason that white section 36 of filter 34 is required in this embodiment.
Figure 4 shows a pulse schedule for the device of Figure 3. As in Figure 2, a 5 solid line represents a broad-band pulse and a dashed line represents a monochromatic pulse. At time To, with filter 34 positioned so that white section 36 is in the optical path of broad-band light 14, shutter 32 is opened, allowing broad-band light 14 to pass through, and to be attenuated by, white section 36. Filter 34 is rotated, until, at time T1, colored section 38 begins to intercept broad-band light 14. At time T2, all of 1o broad-band light 14 is passing through colored section 38, so that the light emerging from the device is substantially monochromatic. At time T3, shutter 32 is closed, terminating the monochromatic pulse.
Figure 5 is a schematic diagram of a variant of the device of Figure 3. In the device of Figure 5, a movable mirror 40 is provided to deflect light passed by shutter 32 to a fixed mirror 41 and a monochromator 42. The device of Figure 5 generates pulses according to the pulse schedule of Figure 6, in which, again, the solid line represents a broad-band pulse and the dashed line represents a monochromatic pulse.
At time To, with mirror 40 withdrawn, shutter 32 is opened, allowing broad-band light 14 to pass through an attenuation filter 44 and thence to the target and the surrounding tissue. Like white region 36 of filter 34, attenuation filter 44 attenuates all wavelengths to substantially the same degree, to provide a broad-band pulse of the proper duration and intensity to heat the target and the surrounding tissue to about 60 C. At time T1, mirror 40 is moved into place, terminating the broad-band pulse, and, deflecting broad-band light 14 so that it passes, via mirror 41, through monochromator 42, thereby initiating the monochromatic pulse. Thus, the monochromatic pulse starts substantially immediately after the termination of the broad-band pulse. Monochromator 42 passes on to the target only a narrow spectral band of light centered on a wavelength of 585 nanometers. At time T2, shutter closes, terminating the monochromatic pulse.
While the invention has been described with respect to a limited number of embodiments, it will be appreciated that many variations, modifications, and other applications of the invention may be made.
Claims (27)
1. Apparatus for selective photothermolysis of a target tissue, the apparatus comprising:
a heat source (10) adapted for first heating the target tissue and tissue surrounding the target tissue above normal body temperature, and then selectively heating the target tissue to a temperature above 70°C.
a heat source (10) adapted for first heating the target tissue and tissue surrounding the target tissue above normal body temperature, and then selectively heating the target tissue to a temperature above 70°C.
2. An apparatus according to claim 1, wherein the heat source (10) is adapted to first heat the target tissue and tissue surrounding the target to between 55°C and 65°C.
3. An apparatus according to claim 1 or claim 2, wherein said heat source (10) uses electromagnetic radiation to provide heating.
4. An apparatus according to claim 3, wherein said electromagnetic radiation comprises microwave radiation.
5. An apparatus according to claim 3 or claim 4, wherein said electromagnetic radiation comprises pulsed radiation.
6. An apparatus according to claim 5, wherein at least one shutter mechanism (32) is used to provide the pulsing.
7. An apparatus according to any of claims 1-6 wherein said heat source is a lamp (10).
8. An apparatus according to claim 7, further comprising a mechanism (34) for wavelength selection.
9. An apparatus according to claim 8, wherein said mechanism (34) for wavelength selection comprises at least one filter (36, 38).
10. Apparatus according to claim 9 wherein said mechanism (34) for wavelength selection comprises at least one monochrometer (42).
11. An apparatus according to any of claims 1-10, wherein the heat source (10) uses pulsed, substantially monochromatic electromagnetic radiation to selectively heat the target tissue.
12. An apparatus according to any of claims 1-11, wherein electromagnetic radiation characterized by a wavelength between about 570 and 610 nanometers is generated by the heat source (10) to provide selective heating.
13. An apparatus according to any of claims 1-3 wherein the heat source is a pulsed heat source.
14. An apparatus according to claim 1, wherein the heat source is comprised of:
a pulsable heat source which heats the target tissue and skin surrounding the target tissue; and a pulsable source of narrowband electromagnetic radiation which irradiates the skin with narrowband electromagnetic radiation to selectively heat said target tissue as compared to said surrounding tissue.
a pulsable heat source which heats the target tissue and skin surrounding the target tissue; and a pulsable source of narrowband electromagnetic radiation which irradiates the skin with narrowband electromagnetic radiation to selectively heat said target tissue as compared to said surrounding tissue.
15. Apparatus according to claim 13 or claim 14 wherein said pulsable heat source comprises a source of broadband electromagnetic radiation which heats the skin.
16. Apparatus according to claim 15 wherein said source of broadband electromagnetic radiation comprises a high intensity lamp (10).
17. Apparatus according to any of claims 14-16 wherein said pulsable source of narrowband electromagnetic radiation comprises:
a lamp (10); and a mechanism (34) for wavelength selection.
a lamp (10); and a mechanism (34) for wavelength selection.
18. Apparatus for selective photothermolysis of a skin target tissue, the apparatus comprising:
a pulsable heat source which heats the skin target tissue and skin surrounding the target tissue to at least 40°C; and a pulsable source of narrowband electromagnetic radiation which irradiates the skin with narrowband electromagnetic radiation, substantially simultaneous with the heating by said pulsable heat source, to selectively heat said target tissue as compared to said surrounding tissue.
a pulsable heat source which heats the skin target tissue and skin surrounding the target tissue to at least 40°C; and a pulsable source of narrowband electromagnetic radiation which irradiates the skin with narrowband electromagnetic radiation, substantially simultaneous with the heating by said pulsable heat source, to selectively heat said target tissue as compared to said surrounding tissue.
19. Apparatus according to claim 18 wherein said heat source comprises a source of broadband electromagnetic radiation which heats the skin.
20. Apparatus according to claim 18 or claim 19 wherein said source of broadband electromagnetic radiation comprises a laser.
21. Apparatus according to claim 18 or claim 19 wherein said source of broadband electromagnetic radiation comprises a microwave source.
22. Apparatus according to any of claims 18-21, wherein said pulsable source of narrowband electromagnetic radiation comprises a pulsed substantially monochromatic source of electromagnetic radiation.
23. Apparatus according to claim 22 wherein said narrowband electromagnetic radiation has a wavelength of between about 570 and 610 nanometers.
24. Apparatus according to any of claims 18-21 wherein said pulsable source of narrowband electromagnetic radiation comprises:
a lamp; and a mechanism for wavelength selection.
a lamp; and a mechanism for wavelength selection.
25. Apparatus according to claim 24 wherein said mechanism for wavelength selection comprises at least one filter.
26. Apparatus according to claim 25 wherein said mechanism for wavelength selection comprises at least one monochrometer.
27. Apparatus according to any of claims 18-26 and including:
a controller unit which controls said heat source and said source of narrowband electromagnetic radiation, for coordinating a sequence of activation of said heat source and said source of electromagnetic radiation.
a controller unit which controls said heat source and said source of narrowband electromagnetic radiation, for coordinating a sequence of activation of said heat source and said source of electromagnetic radiation.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US08/707,562 US5759200A (en) | 1996-09-04 | 1996-09-04 | Method of selective photothermolysis |
| PCT/US1998/008657 WO1999056824A1 (en) | 1996-09-04 | 1998-04-30 | Method of selective photothermolysis |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2330029A1 CA2330029A1 (en) | 1999-11-11 |
| CA2330029C true CA2330029C (en) | 2012-08-07 |
Family
ID=26794099
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA2330029A Expired - Fee Related CA2330029C (en) | 1996-09-04 | 1998-04-30 | Method of selective photothermolysis |
Country Status (11)
| Country | Link |
|---|---|
| US (1) | US5759200A (en) |
| EP (1) | EP1079895A4 (en) |
| JP (1) | JP4153165B2 (en) |
| CN (1) | CN1193805C (en) |
| AU (1) | AU748623B2 (en) |
| BR (1) | BR9815839A (en) |
| CA (1) | CA2330029C (en) |
| EA (1) | EA002506B1 (en) |
| IL (2) | IL139336A0 (en) |
| MX (1) | MXPA00010474A (en) |
| WO (1) | WO1999056824A1 (en) |
Families Citing this family (81)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| GB9618051D0 (en) * | 1996-08-29 | 1996-10-09 | Sls Wales Ltd | Wrinkle removal |
| US5759200A (en) * | 1996-09-04 | 1998-06-02 | Azar; Zion | Method of selective photothermolysis |
| US6214034B1 (en) * | 1996-09-04 | 2001-04-10 | Radiancy, Inc. | Method of selective photothermolysis |
| US6653618B2 (en) | 2000-04-28 | 2003-11-25 | Palomar Medical Technologies, Inc. | Contact detecting method and apparatus for an optical radiation handpiece |
| US8182473B2 (en) | 1999-01-08 | 2012-05-22 | Palomar Medical Technologies | Cooling system for a photocosmetic device |
| US6273884B1 (en) * | 1997-05-15 | 2001-08-14 | Palomar Medical Technologies, Inc. | Method and apparatus for dermatology treatment |
| US6517532B1 (en) | 1997-05-15 | 2003-02-11 | Palomar Medical Technologies, Inc. | Light energy delivery head |
| NO972244L (en) * | 1997-05-15 | 1998-11-16 | Photocure | Device for illumination of a defined area |
| JPH11104145A (en) * | 1997-09-30 | 1999-04-20 | Nidek Co Ltd | Laser therapeutic device |
| AUPP176898A0 (en) * | 1998-02-12 | 1998-03-05 | Moldflow Pty Ltd | Automated machine technology for thermoplastic injection molding |
| EP1566149A1 (en) | 1998-03-12 | 2005-08-24 | Palomar Medical Technologies, Inc. | System for electromagnetic radiation of the skin |
| ES2403359T3 (en) * | 1998-03-27 | 2013-05-17 | The General Hospital Corporation | Procedure and apparatus for the selective determination of lipid rich tissues |
| US6306130B1 (en) | 1998-04-07 | 2001-10-23 | The General Hospital Corporation | Apparatus and methods for removing blood vessels |
| US6059820A (en) | 1998-10-16 | 2000-05-09 | Paradigm Medical Corporation | Tissue cooling rod for laser surgery |
| US6514242B1 (en) * | 1998-12-03 | 2003-02-04 | David Vasily | Method and apparatus for laser removal of hair |
| RU2181571C2 (en) | 1999-03-18 | 2002-04-27 | Закрытое акционерное общество "LC" | Device and method for performing therapeutic and cosmetic phototreatment of biological tissue |
| IL149874A0 (en) | 1999-12-02 | 2002-11-10 | Radiancy Inc | Selective photothermolysis |
| IL150604A0 (en) * | 2000-01-25 | 2003-02-12 | Palomar Medical Tech Inc | Method and apparatus for medical treatment utilizing long duration electromagnetic radiation |
| GB2370229A (en) * | 2000-12-22 | 2002-06-26 | Icn Photonics Ltd | Light delivery system for improving the appearance of skin |
| JP2005502385A (en) * | 2000-12-28 | 2005-01-27 | パロマー・メディカル・テクノロジーズ・インコーポレーテッド | Method and apparatus for performing skin therapy EMR treatment |
| US7090497B1 (en) | 2001-02-21 | 2006-08-15 | Harris David M | Method of periodontal laser treatment |
| US6888319B2 (en) * | 2001-03-01 | 2005-05-03 | Palomar Medical Technologies, Inc. | Flashlamp drive circuit |
| EP1414516A2 (en) * | 2001-06-26 | 2004-05-06 | Photomed Technologies, Inc. | Therapeutic methods using electromagnetic radiation |
| US20040158300A1 (en) * | 2001-06-26 | 2004-08-12 | Allan Gardiner | Multiple wavelength illuminator having multiple clocked sources |
| AU2002316500A1 (en) | 2001-07-02 | 2003-01-21 | Palomar Medical Technologies, Inc. | Laser device for medical/cosmetic procedures |
| US20030109787A1 (en) * | 2001-12-12 | 2003-06-12 | Michael Black | Multiple laser diagnostics |
| US20030109860A1 (en) * | 2001-12-12 | 2003-06-12 | Michael Black | Multiple laser treatment |
| US20040082940A1 (en) * | 2002-10-22 | 2004-04-29 | Michael Black | Dermatological apparatus and method |
| US20040127892A1 (en) * | 2002-01-31 | 2004-07-01 | Harris David M. | Periodontal laser and methods |
| IL163946A0 (en) * | 2002-03-12 | 2005-12-18 | Gen Hospital Corp | Method and apparatus for hair growth managment |
| US20080177359A1 (en) * | 2002-05-03 | 2008-07-24 | Advanced Light Technology, Llc. | Differential photochemical and photomechanical processing |
| US20070038206A1 (en) * | 2004-12-09 | 2007-02-15 | Palomar Medical Technologies, Inc. | Photocosmetic device |
| US7135033B2 (en) | 2002-05-23 | 2006-11-14 | Palomar Medical Technologies, Inc. | Phototreatment device for use with coolants and topical substances |
| BR0312430A (en) | 2002-06-19 | 2005-04-26 | Palomar Medical Tech Inc | Method and apparatus for treating skin and subcutaneous conditions |
| WO2004033040A1 (en) * | 2002-10-07 | 2004-04-22 | Palomar Medical Technologies, Inc. | Apparatus for performing photobiostimulation |
| US7354433B2 (en) * | 2003-02-28 | 2008-04-08 | Advanced Light Technologies, Llc | Disinfection, destruction of neoplastic growth, and sterilization by differential absorption of electromagnetic energy |
| US20110040295A1 (en) * | 2003-02-28 | 2011-02-17 | Photometics, Inc. | Cancer treatment using selective photo-apoptosis |
| DE202004021226U1 (en) | 2003-03-27 | 2007-07-26 | The General Hospital Corp., Boston | Device for dermatological treatment and fractional surface renewal of the skin |
| US7282060B2 (en) | 2003-12-23 | 2007-10-16 | Reliant Technologies, Inc. | Method and apparatus for monitoring and controlling laser-induced tissue treatment |
| US7184184B2 (en) * | 2003-12-31 | 2007-02-27 | Reliant Technologies, Inc. | High speed, high efficiency optical pattern generator using rotating optical elements |
| US7196831B2 (en) * | 2003-12-31 | 2007-03-27 | Reliant Technologies, Inc. | Two-dimensional optical scan system using a counter-rotating disk scanner |
| US7090670B2 (en) * | 2003-12-31 | 2006-08-15 | Reliant Technologies, Inc. | Multi-spot laser surgical apparatus and method |
| US7372606B2 (en) | 2003-12-31 | 2008-05-13 | Reliant Technologies, Inc. | Optical pattern generator using a single rotating component |
| JP5065005B2 (en) | 2004-04-01 | 2012-10-31 | ザ ジェネラル ホスピタル コーポレイション | Method and apparatus for dermatological treatment and tissue remodeling |
| US20070016181A1 (en) | 2004-04-29 | 2007-01-18 | Van Der Weide Daniel W | Microwave tissue resection tool |
| US7467015B2 (en) | 2004-04-29 | 2008-12-16 | Neuwave Medical, Inc. | Segmented catheter for tissue ablation |
| US7244254B2 (en) * | 2004-04-29 | 2007-07-17 | Micrablate | Air-core microwave ablation antennas |
| US20070055224A1 (en) * | 2004-04-29 | 2007-03-08 | Lee Fred T Jr | Intralumenal microwave device |
| US7413572B2 (en) | 2004-06-14 | 2008-08-19 | Reliant Technologies, Inc. | Adaptive control of optical pulses for laser medicine |
| FR2878185B1 (en) * | 2004-11-22 | 2008-11-07 | Sidel Sas | PROCESS FOR MANUFACTURING CONTAINERS COMPRISING A HEATING STEP BY MEANS OF A COHERENT ELECTROMAGNETIC RADIATION BEAM |
| US7856985B2 (en) | 2005-04-22 | 2010-12-28 | Cynosure, Inc. | Method of treatment body tissue using a non-uniform laser beam |
| WO2006127847A2 (en) * | 2005-05-24 | 2006-11-30 | Micrablate, Llc | Microwave surgical device |
| AU2006281029A1 (en) * | 2005-08-17 | 2007-02-22 | Y.K. Holdings Ltd. | Lice extermination system and method |
| JP2009509140A (en) | 2005-09-15 | 2009-03-05 | パロマー・メデイカル・テクノロジーズ・インコーポレーテツド | Skin optical determination device |
| US8672932B2 (en) | 2006-03-24 | 2014-03-18 | Neuwave Medical, Inc. | Center fed dipole for use with tissue ablation systems, devices and methods |
| EP1998699A1 (en) * | 2006-03-24 | 2008-12-10 | Neuwave Medical, Inc. | Energy delivery system |
| EP1998698B1 (en) | 2006-03-24 | 2020-12-23 | Neuwave Medical, Inc. | Transmission line with heat transfer ability |
| US11389235B2 (en) | 2006-07-14 | 2022-07-19 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
| US10376314B2 (en) | 2006-07-14 | 2019-08-13 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
| US7586957B2 (en) | 2006-08-02 | 2009-09-08 | Cynosure, Inc | Picosecond laser apparatus and methods for its operation and use |
| US20080161745A1 (en) * | 2006-09-08 | 2008-07-03 | Oliver Stumpp | Bleaching of contrast enhancing agent applied to skin for use with a dermatological treatment system |
| US20080172111A1 (en) * | 2007-01-16 | 2008-07-17 | The General Hospital Corporation | Method and apparatus for selective photothermolysis of veins |
| FR2913210B1 (en) * | 2007-03-02 | 2009-05-29 | Sidel Participations | IMPROVEMENTS IN THE HEATING OF PLASTIC MATERIALS BY INFRARED RADIATION |
| FR2917005B1 (en) * | 2007-06-11 | 2009-08-28 | Sidel Participations | HEATING FACILITY FOR PREFORMING BODIES FOR BLOWING CONTAINERS |
| US20110224656A1 (en) * | 2008-04-03 | 2011-09-15 | The General Hospital Corporation | Method and apparatus for selective photothermolysis of veins |
| US20100047734A1 (en) * | 2008-08-20 | 2010-02-25 | PathoLase, Inc. | Periodontal laser treatment and laser applicator |
| US8939966B2 (en) * | 2008-08-21 | 2015-01-27 | University Of Florida Research Foundation, Inc. | Differential laser-induced perturbation (DLIP) for bioimaging and chemical sensing |
| US9919168B2 (en) | 2009-07-23 | 2018-03-20 | Palomar Medical Technologies, Inc. | Method for improvement of cellulite appearance |
| WO2011017168A2 (en) | 2009-07-28 | 2011-02-10 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
| ES2856026T3 (en) | 2010-05-03 | 2021-09-27 | Neuwave Medical Inc | Power supply systems |
| CN107224325B (en) | 2011-12-21 | 2020-09-01 | 纽华沃医药公司 | Energy delivery system and use thereof |
| US9780518B2 (en) | 2012-04-18 | 2017-10-03 | Cynosure, Inc. | Picosecond laser apparatus and methods for treating target tissues with same |
| JP2014018320A (en) * | 2012-07-13 | 2014-02-03 | Scandinavia Corp | Thermal light irradiation device |
| WO2014145707A2 (en) | 2013-03-15 | 2014-09-18 | Cynosure, Inc. | Picosecond optical radiation systems and methods of use |
| JP6857187B2 (en) | 2015-10-26 | 2021-04-14 | ニューウェーブ メディカル, インコーポレイテッドNeuwave Medical, Inc. | Energy supply system and its use |
| ES2854935T3 (en) | 2016-04-15 | 2021-09-23 | Neuwave Medical Inc | Power delivery system |
| US10806513B2 (en) * | 2018-01-16 | 2020-10-20 | Bin Rao | Methods and apparatus for optimizing selective photothermolysis |
| US11672596B2 (en) | 2018-02-26 | 2023-06-13 | Neuwave Medical, Inc. | Energy delivery devices with flexible and adjustable tips |
| WO2019165426A1 (en) | 2018-02-26 | 2019-08-29 | Cynosure, Inc. | Q-switched cavity dumped sub-nanosecond laser |
| US10799292B2 (en) * | 2018-05-04 | 2020-10-13 | Bin Rao | High power tunable optical parametric oscillator for selective photothermolysis laser surgeries |
| US11832879B2 (en) | 2019-03-08 | 2023-12-05 | Neuwave Medical, Inc. | Systems and methods for energy delivery |
Family Cites Families (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| HU186081B (en) * | 1981-09-02 | 1985-05-28 | Fenyo Marta | Process and apparatus for stimulating healing of pathologic points on the surface of the body first of all of wounds, ulcera and other epithelial lesions |
| JPS60137342A (en) * | 1983-12-27 | 1985-07-20 | オリンパス光学工業株式会社 | Electronic scope |
| ATE51730T1 (en) * | 1984-10-25 | 1990-04-15 | Candela Laser Corp | TUNABLE LONG-PULSE DYE LASER. |
| WO1991013652A1 (en) * | 1990-03-14 | 1991-09-19 | Candela Laser Corporation | Apparatus for treating abnormal pigmentation of the skin |
| SE465953B (en) * | 1990-04-09 | 1991-11-25 | Morgan Gustafsson | DEVICE FOR TREATMENT OF UNDESECTED EXTERNAL ACCOMMODATIONS |
| US5071417A (en) * | 1990-06-15 | 1991-12-10 | Rare Earth Medical Lasers, Inc. | Laser fusion of biological materials |
| US5860967A (en) * | 1993-07-21 | 1999-01-19 | Lucid, Inc. | Dermatological laser treatment system with electronic visualization of the area being treated |
| US5604629A (en) * | 1993-07-27 | 1997-02-18 | The United States Of America As Represented By The Secretary Of The Navy | Discrete vacuum ultra violet reflective interference filter |
| US5441531A (en) * | 1993-10-18 | 1995-08-15 | Dusa Pharmaceuticals Inc. | Illuminator and methods for photodynamic therapy |
| US5521392A (en) * | 1994-04-29 | 1996-05-28 | Efos Canada Inc. | Light cure system with closed loop control and work piece recording |
| US5759200A (en) * | 1996-09-04 | 1998-06-02 | Azar; Zion | Method of selective photothermolysis |
-
1996
- 1996-09-04 US US08/707,562 patent/US5759200A/en not_active Expired - Lifetime
-
1998
- 1998-04-30 IL IL13933698A patent/IL139336A0/en unknown
- 1998-04-30 CA CA2330029A patent/CA2330029C/en not_active Expired - Fee Related
- 1998-04-30 CN CNB988140012A patent/CN1193805C/en not_active Expired - Fee Related
- 1998-04-30 WO PCT/US1998/008657 patent/WO1999056824A1/en active IP Right Grant
- 1998-04-30 JP JP2000546842A patent/JP4153165B2/en not_active Expired - Fee Related
- 1998-04-30 BR BR9815839-2A patent/BR9815839A/en not_active IP Right Cessation
- 1998-04-30 EP EP98918852A patent/EP1079895A4/en not_active Ceased
- 1998-04-30 EA EA200001132A patent/EA002506B1/en not_active IP Right Cessation
- 1998-04-30 MX MXPA00010474A patent/MXPA00010474A/en unknown
- 1998-04-30 AU AU71695/98A patent/AU748623B2/en not_active Ceased
-
2000
- 2000-10-29 IL IL139336A patent/IL139336A/en not_active IP Right Cessation
Also Published As
| Publication number | Publication date |
|---|---|
| BR9815839A (en) | 2000-12-26 |
| AU748623B2 (en) | 2002-06-06 |
| IL139336A (en) | 2008-11-03 |
| MXPA00010474A (en) | 2002-10-17 |
| JP2002513658A (en) | 2002-05-14 |
| CN1299295A (en) | 2001-06-13 |
| EA002506B1 (en) | 2002-06-27 |
| CA2330029A1 (en) | 1999-11-11 |
| EP1079895A1 (en) | 2001-03-07 |
| US5759200A (en) | 1998-06-02 |
| IL139336A0 (en) | 2001-11-25 |
| CN1193805C (en) | 2005-03-23 |
| AU7169598A (en) | 1999-11-23 |
| EA200001132A1 (en) | 2001-04-23 |
| JP4153165B2 (en) | 2008-09-17 |
| EP1079895A4 (en) | 2005-06-22 |
| WO1999056824A1 (en) | 1999-11-11 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2330029C (en) | Method of selective photothermolysis | |
| US6579283B1 (en) | Apparatus and method employing a single laser for removal of hair, veins and capillaries | |
| EP1077741B1 (en) | Selective photothermolysis of the skin | |
| AU742982B2 (en) | Pulsed filament lamp for dermatological treatment | |
| US6080147A (en) | Method of employing a flashlamp for removal of hair, veins and capillaries | |
| US5968034A (en) | Pulsed filament lamp for dermatological treatment | |
| US6149645A (en) | Apparatus and method employing lasers for removal of hair | |
| KR100376650B1 (en) | Alexander laser system for the treatment of skin pathological specimens | |
| US7241291B2 (en) | Method and system for skin treatment using light energy and skin deformation | |
| CA2644512A1 (en) | Method and apparatus for light-based hair removal | |
| US6168589B1 (en) | Apparatus and method employing a single laser for removal of hair | |
| US6217572B1 (en) | Apparatus and method employing lasers for removal of hair | |
| US6165171A (en) | Apparatus and method employing lasers for removal of hair | |
| CA2443055A1 (en) | Therapeutic treatment device | |
| AU2002300881B2 (en) | Method and apparatus for heating a target | |
| KR100504990B1 (en) | Apparatus for selective photothermolysis |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKLA | Lapsed |
Effective date: 20160502 |